X-ray generator

ABSTRACT

The electron beam corresponding to radiation intensity data  112  is output from an electron source  103  by supplying high energy pulse p- 1  through p-n corresponding to the radiation intensity data  112  of the radiation field to electron source  103  from power source  108 . This electron beam is deflected to be incident in parallel to the medial axis of the X-ray target tube by a deflection means comprising electromagnets, X-ray beam x- 1  through x-n which electron beam collides to the inner wall of X-ray target tube  104 - 1  through  104 - n , and have desired intensity is irradiated.

BACKGROUND OF THE INVENTION

1. Field of the Invention

The present invention concerns an X-ray generator irradiating the X-ray beam which the radiation intensity is modulated, in particular, it relates to an X-ray generator can form a new radiation field by bundling up a plurality of X-ray tubes that the radiation field of the X-ray beam is narrow and can set the radiation intensity individually. Even more particularly, the present invention relates to an X-ray generator which is suitable for an X-ray therapeutic apparatus with one or more the X-ray generators.

2. Description of the Related Art

An intensity modulation radiation therapy (it is abbreviated to IMRT as follows.) can reduce a radiation dose to normal tissues around the lesion portion by changing such as a radiation angular degree, a radiation field and a radiation intensity of radioactive rays according to a shape of the lesion portion, so that the radioactive rays concentrate on the lesion portion. The apparatus for IMRT which modulates intensity by a multi-leaf collimator placed between a radiation aperture and a patient is known (for example, it is illustrated to Japanese Unexamined Patent Application Publication No. H09-239044, Japanese Unexamined Patent Application Publication No. H10-071214, Japanese Unexamined Patent Application Publication No. 2002-153567 and Japanese Unexamined Patent Application Publication No. 2001-070466).

A therapy apparatus as claimed in Japanese Unexamined Patent Application Publication No. H09-239044, as shown in FIG. 15, comprises a multi-leaf collimator 13 controlled by a gantry 11 and a multi-leaf collimator control unit 12. The therapy apparatus can obtain the dose distribution corresponding to the three-dimensional shape of the tumor of the patient by irradiating radiation beams around a patient while changing a shape of the radiation field of the multi-leaf collimator 13 in accordance with rotation angle of the gantry 11.

A method of obtaining the dose distribution that the intensity of the radiation beams change optimally is described in Japanese Unexamined Patent Application Publication No. H10-071214. The method divides a three-dimensional intensity map of the radiation field into many sections of the intensity, and makes the intensity map of the radiation beam every the section. The intensity map is sliced to a matrix showing whether the radiation is required or not. The shape of the aperture of the collimator is set according to the matrix. Afterward X-rays is irradiated for the object. This radiation apparatus obtains the optimum dose distribution by repeating this process.

A method of obtaining the dose distribution raising the resolution of the radiation dose in the bound of the treatment domain is described in Japanese Unexamined Patent Application Publication No. 2002-153567. The method divides a treatment domain into a plurality of cells having the predetermined treatment intensity level. For the cell including the critical tissues which places in the bound of the treatment domain out of divided cells, the leaf of the multi-leaf collimator moves to the position of the edge margin which is set the position of the middle of the cell not the edge of the cell, the radioactive rays are irradiated.

A method of irradiating with radioactive rays described in Japanese Unexamined Patent Application Publication No. 2001-070466 resolves further the two-dimensional radiation intensity distribution quantized by levels of the predetermined integer number into a plurality of the two-dimensional radiation intensity distributions of relative intensity 1. In each two-dimensional radioactive rays distribution generated by resolving, there are only shielding object cells and radiation object cells, besides the radiation intensity to an radiation object cells is equal (relative intensity 1). After this, the multi-leaf collimator is placed according to the generated two-dimensional radioactive rays distribution, the radiation rays are irradiated.

However, each invention described in Japanese Unexamined Patent Application Publication No. H09-239044, Japanese Unexamined Patent Application Publication No. H10-071214, Japanese Unexamined Patent Application Publication No. 2002-153567 and Japanese Unexamined Patent Application Publication No. 2001-070466 shows the manner obtaining cumulatively the intensity distribution of required radiation dose by repeating the radiation with changing the shape of the aperture of the multi-leaf collimator. According to the invention of Japanese Unexamined Patent Application Publication No. H09-239044, the dose distribution modulated the radiation intensity in the three-dimensional space can be obtained by the rotation of the gantry, as the two-dimensional plane radiation intensity is equal, the intensity modulation in the two-dimensional plane cannot be obtained. Therefore, the accuracy of dose distribution obtained in the three-dimensional space is not sufficient.

The invention described in Japanese Unexamined Patent Application Publication No. H10-071214, Japanese Unexamined Patent Application Publication No. 2002-153567 and Japanese Unexamined Patent Application Publication No. 2001-070466 can obtain an intensity modulation in the two-dimensional plane by multiple radiation, but the radiation has to be performed at least the number of times according to an intensity level. When there is a plurality of shielding domains in the direction of the leaf motion, even if the intensity level is one, the leaf is moved, and the radiation has to be performed multiple times.

In late years, with the improvement of the imaging diagnostic technology such as CT scanner, a three-dimensional shape of the lesion portion can be grasped in detail. With this, it becomes required to raise an accuracy of the radiation therapy adapting for a symptom of each part of the lesion portion. However, when an accuracy of the radiation therapy is going to be raised by using the multi-leaf collimator, a radiation number of times will be increased, burdens of the patient increase to need time for a treatment. Even more particularly, if a treatment time becomes long, there is a limit in the conventional method of improving treatment accuracy by increasing a radiation number of times because it becomes difficult to fix a lesion portion.

It is necessary to irradiate with a rotational transfer of the gantry to get a dose distribution corresponding to the three-dimensional shape of the lesion portion in the invention described in Japanese Unexamined Patent Application Publication No. H09-239044, Japanese Unexamined Patent Application Publication No. H10-071214, Japanese Unexamined Patent Application Publication No. 2002-153567 and Japanese Unexamined Patent Application Publication No. 2001-070466. However, because the gantry is heavy, the backlashes and arcuations occur easily while the gantry rotates. As shown in Japanese Unexamined Patent Application Publication No. 2002-153567, when the resolution higher than ⅓ cm is required, the three-dimensional radiation of radioactive rays after a gantry rotational transferred has a problem in respect of accuracy.

Also, because the leaf of the multi-leaf collimator is rectangular, when the treatment domain has unevenness, it is difficult to position the leaf along the bound of the treatment domain. Even more particularly, there is a problem to injure normal tissues of the bound vicinity because a leaf malfunctions in the location with a rippling dose distribution in the bound part of the radiation domain.

It is an object of the present invention to provide the X-ray generator which can obtain immediately a two-dimensional dose distribution which the intensity is finely modulated corresponding to the desired radiation dose for X-ray therapy to each part of the lesion portion by solving previously described problems. Even more particularly, it is an object of the present invention to provide the X-ray generator which is suitable for X-ray generator in the X-ray therapeutic apparatus.

SUMMARY OF THE INVENTION

The X-ray generator comprises a power source outputting high energy pulses, an electron source irradiating high energy electron beams by the high energy pulses, a microwave source supplying a high voltage microwave to the electron source, an X-ray source bundling up a plurality of X-ray tubes irradiating X-ray by a collision of the high-energy electron beams, arranging to continue the radiation fields of the X-ray tubes, a deflection means deflecting the direction of the high energy electron beams so that the high energy electron beams are incident in parallel to the medial axis of the X-ray tubes, and are incident on the X-ray tubes sequentially, a data setting the radiation intensity of the X-ray tube so that the predetermined dose distribution is obtained in the field of the X-ray tube and a control means setting up the high energy pulse width according to the radiation intensity data, synchronizing a timing to output the high energy pulse and a timing to irradiate the electron beams and a timing to excite the deflection means.

The deflection means comprises a first deflection electromagnet deflecting the high energy electron beam to an inlet aperture of any X-ray tubes and a second deflection electromagnet deflecting the high energy electron beams deflected by the first deflection electromagnet so that the high energy electron beams are incident in parallel to the medial axis of the X-ray tubes.

The X-ray source comprises the X-ray tubes arranging in line, the high energy electron beams are sequentially irradiated from one end of the X-rays tubes to the another end.

The deflection means comprises a deflection electromagnet deflecting the high energy electron beam to an inlet aperture of any X-ray tubes and the X-ray tube arranging radially so that the direction of the high energy electron beams deflected by the deflection electromagnet are in parallel to the medial axis of the X-ray tubes. The deflection means comprises a quadrupole electromagnet.

The X-ray tube comprises a truncated cone shape having a smaller diameter of the outlet aperture than the inlet aperture, and acts as an X-ray target tube irradiating X-ray beams by the collision of high energy electron beams with the inner wall of the X-ray tube.

The X-ray source comprises the X-ray tubes arranging so that radiation fields of ½ width for the maximum radiation intensity are adjacent in succession. The X-ray generator of the present invention, applied to the X-ray therapeutic apparatus, one or more the X-ray generators being installed in different positions of the three-dimensional space including the treatment couch, X-rays are irradiated intensively on the lesion portion of a patient fixed on the treatment couch in the space.

The X-ray generator of the present invention, applied to the X-ray therapeutic apparatus, comprises the translation means moving the treatment couch in parallel perpendicularly to the X-ray generator and the control means which control by synchronizing the X-ray generator and the translation means.

The X-ray generator of the present invention, applied to the X-ray therapeutic apparatus, is applied to the X-ray therapeutic apparatus being able to vary a relative position of the lesion portion of a patient fixed on a treatment couch and the X-ray generator installed in the X-ray head, irradiating X-rays to the lesion portion of the patient.

According to the X-ray generator of the present invention, it can provide immediately desired two-dimensional dose distribution by subdividing the radiation dose to need for each part of the lesion portion without using multi-leaf collimator. Even more particularly, the present invention can provide the X-ray therapeutic apparatus which is able to treat effectively a lesion portion with easing burdens of a patient by shortening treatment time and with holding down a dosage to normal cell.

The preferred embodiments of the X-ray generator and X-ray therapeutic apparatus with the X-ray generators will be described with reference to the accompanying drawings in detail as follows.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1 is a block diagram of the X-ray generator concerning the preferred embodiment 1 of the present invention;

FIG. 2 is a diagram describing the state to modulate the intensity of the radiation field of the X-ray target tube array in accordance with the radiation intensity data of the radiation field concerning the preferred embodiment 1 of the present invention;

FIG. 3 is a diagram describing the deflection of the electron beam by the deflection electromagnet concerning the preferred embodiment 1 of the present invention;

FIG. 4 is a configuration diagram of the X-ray target tube concerning the preferred embodiment 1 of the present invention;

FIG. 5 is a diagram describing the radiation field of the X-ray target tube concerning the preferred embodiment 1 of the present invention;

FIG. 6 is a diagram describing the radiation field of the X-ray target tube array concerning the preferred embodiment 1 of the present invention;

FIG. 7 is a diagram describing the radiation intensity data of the treatment field and the radiation intensity data of the radiation field concerning the preferred embodiment 1 of the present invention;

FIG. 8 is a perspective view which shows the constitution example of the X-ray therapeutic apparatus which attached the X-ray generator concerning the preferred embodiment 1 of the present invention;

FIG. 9 is a flow chart which shows the routine of the radiation control program of the X-ray generator concerning the preferred embodiment 1 of the present invention;

FIG. 10 is a flow chart which shows the routine of the treatment execution program of the control unit concerning the preferred embodiment 1 of the present invention;

FIG. 11 is a perspective diagram which shows the example of the other X-ray therapeutic apparatus which attached the X-ray generator concerning the preferred embodiment 1 of the present invention to a gantry;

FIG. 12 is a block diagram of the X-ray generator concerning the preferred embodiment 2 of the present invention;

FIG. 13 is a cross-sectional view which cut the quadrupole electromagnet concerning the preferred embodiment 2 of the present invention in perpendicular plane in the direction of the electron beam;

FIG. 14 is a diagram describing the radiation field of the X-ray target array concerning the preferred embodiment 2 of the present invention; and

FIG. 15 is a perspective view which shows a conventional intensity modulated arc therapy with dynamic multi-leaf collimation.

DESCRIPTION OF THE PREFERRED EMBODIMENTS Detailed Description of the Preferred Embodiment 1

FIG. 1 shows the schematic representation showing a constitution of the X-ray generator concerning the preferred embodiment 1 of the present invention. In FIG. 1, the X-ray generator 101 comprises an electron source (hereinafter referred to as an electron gun) 103 irradiating high energy electron beams to a vacuum chamber 102, the X-ray target tube array 105 comprises a plurality of X-ray target tubes 104-1 through 104-n arranging in line which irradiates X-ray beams by colliding the high energy electron beams irradiated by the electron gun 103, the first deflection electromagnet 106 and the second deflection electromagnet 107 which deflect the high energy electron beams which are irradiated the electron gun 103. A power source 108 outputting the high energy pulse to the electron gun 103 by a predetermined timing, a microwave source 110 supplying the high voltage microwave to the electron gun 103 and a controller 109 controlling the power source 108, the microwave source 110, the first deflection electromagnet 106 and the second deflection electromagnet 107 are comprised by a exterior of the vacuum chamber 102. A radiation control program 111 and a radiation intensity data 113 of the treatment field which comprises a radiation intensity data 112 of the radiation field of the X-ray target tube array 105 are stored in the controller 109. The radiation intensity data 112 of the radiation field presents a radiation dose of each X-ray target tube 104-1 through 104-n comprising the X-ray target tube array 105. The radiation control program 111 controls the high voltage microwave source 110, the excitation of the first deflection electromagnet 106 and the second deflection electromagnet 107 and the width of the high energy pulse outputting from the power source 108 so that high energy electron beams which are irradiated from the electron gun 103 reflect in turn on the X-ray target tube 104-1 through 104-n arranging in line.

FIG. 2 shows the state of the modulated intensity for the radiation field of the X-ray target tube array in accordance with the radiation intensity data of the radiation field concerning the preferred embodiment 1 of the present invention. In FIG. 2, when the high energy pulse p-1 through p-n corresponding to the desired radiation dose is output from the power source 108, the electron beams corresponding to the high energy pulse p-1 through p-n are irradiated in turn from the electron gun 103. The X-ray beams x-1 through x-n are irradiated by the electron beams colliding to the inner wall of the X-ray target tube 104-1 through 104-n comprising of the X-ray target tube array 105. The intensity of the X-ray beams x-1 through x-n is modulated corresponding to the radiation intensity data 112 of the radiation field. The first deflection electromagnet 106 and the second deflection electromagnet 107 shown in FIG. 1 are the parallel plate electromagnets respectively. The first deflection electromagnet 106 acts to bend the high energy electron beams to the direction of the desired target tube in the X-ray target tube array 105. The second deflection electromagnet 107 deflects the high energy electron beams bent the direction with the first deflection electromagnet in parallel to the medial axis of the desired X-ray target tube.

FIG. 3 shows the deflecting state of the high energy electron beams. In FIG. 3, a rectangular domain 106 a shows the magnetic field of the magnetic flux density B₁ generated by the first deflection electromagnet 106, and a rectangular domain 107 a shows the magnetic field of the magnetic flux density B₂ generated by the second deflection electromagnet 107. The direction of the magnetic field 106 a is set up an positive direction (the direction which is from back to front of the space) of the Z-axis where is perpendicular to a XY plane, the direction of the magnetic field 107 a is set up the opposite direction (the direction which is from front to back of the space).

In FIG. 3, when the electron irradiated from the electron gun 103 penetrates at the velocity v at the point P₀ (0,0) of the magnetic field of this magnetic flux density B₁, Lorentz force shown in expression (1) acts on the electron.

F=e[(v×B ₁)]  (1)

The direction of the force is the positive direction of a Y-axis. The force acts on the parallel direction to the XY plane without Z component. The electron uniform motions over a circular orbit of radius r₁ because this Lorentz force and the centrifugal force with the electron velocity keep a balance. In other words, the motion equation is presented in (2).

$\begin{matrix} {\frac{{mv}^{2}}{r_{1}} = {evB}_{1}} & (2) \end{matrix}$

Here, m is the mass of a motioning electron, v is the speed of an electron, e is the electric charge of an electron. The coordinate of the point which the electron crosses the edge of the magnetic field 106 a is P₁ (l₁, dl₁). In other words, the electron is biased the distance of dl₁ toward a y-axis direction by the magnetic field 106 a. The electron moves over a circumference expressed in the next equation.

X ²+(y−r ₁)² =r ₁ ²

Therefore, the next equation is formed.

I ₁ ²+(dl ₁ −r ₁)² =r ₁ ²  (3)

Thus,

dl ₁ =r ₁[1−{1−(l ₁ /r ₁)²}^(1/2)]  (4)

But, the next condition is kept.

l₁≦r₁

Because the electron velocity is almost equal to the velocity of light, the special relativity is applied, the next equation is provided from equation (2).

$\begin{matrix} {r_{1} = {\frac{mv}{{eB}_{1}} = {{\frac{m_{0}}{\sqrt{1 - \left( \frac{v}{c} \right)^{2}}} \times \frac{v}{{eB}_{1}}} = {\frac{m_{0}v}{e \times \sqrt{1 - \left( \frac{v}{c} \right)^{2}}} \times \frac{1}{B_{1}}}}}} & (5) \end{matrix}$

Here, m₀ presents the rest mass of electron, c presents the velocity of light. Also, the electron velocity v accelerated in the voltage V is given by the following equation.

$\begin{matrix} {\frac{v}{c} = \sqrt{1 - \frac{1}{\left( {1 + \frac{eV}{m_{0}c^{2}}} \right)^{2}}}} & (6) \end{matrix}$

Because the deflection angle θ₁ of the motion direction of an electron to the X-axis at the point P₁ is the tangent of the point P₁ of the quadratic curve x²+(y−r₁)²=r₁ ², θ₁ is expressed as follows.

$\begin{matrix} {\frac{y}{x_{p_{1}{({l_{1},{dl}_{1}})}}} = {{\tan \; \theta_{1}} = {\left( {- \frac{x}{y - r_{1}}} \right)_{P_{1}{({l_{1},{dl}_{1}})}} = \frac{l_{1}}{r_{1} - {dl}_{1}}}}} & (7) \\ {\theta_{1} = {\tan^{- 1}\left\lbrack {l_{1}/\left( {r_{1} - {dl}_{1}} \right)} \right\rbrack}} & (8) \end{matrix}$

Because, in the domain without a magnetic field, an electron motion is the linear uniform motion in parallel to the XY plane, the electron passed the point P₁ (l₁, dl₁) runs to the straight direction, and arrived at the point P₂. Here, the coordinate of the point P₂ is as follows.

P ₂(x,y)=P ₂(l ₁ +D,dl ₁ +D tan θ₁)

Here, D presents the interval of the edge of the magnetic field 106 a and the magnetic field 107 a. The electron which reached the point P₂ acts uniform motion over a circular orbit of the radius r₂ around the point C₂ by the magnetic field of the magnetic flux density B₂. An electron which reached the point P₃ is biased a distance of dl₂ toward the Y-axis from the point P₂. In other words, the distance of the bias from the X-axis when the electron passes point P₃ (in other words, the value of a Y coordinate) is as follows.

dl=dl ₁ D tan θ₁ +dl ₂  (9)

Also, when the difference of the point P₃ and the point C₂ toward the X-axis is Δx, because the point P₂ P₂(x, y)=P₂ (l₁+D, dl₁+Dtan θ₁) and the point P₃P₃(x, y)=P₃ (l₁+D+l₂−Δx,dl₁+Dtan θ₁+dl₂) located on the circular orbit of radius r₂, the biased distance of electron dl₂ by magnetic flux density B₂ can be expressed Equation (10).

$\begin{matrix} \begin{matrix} {{dl}_{2} = {{{r_{2}\cos \; \theta_{2}} - {r_{2}\cos \; \theta_{1}}} = {{r_{2}\sqrt{1 - {\sin^{2}\theta_{2}}}} - {r_{2}\sqrt{1 - {\sin^{2}\theta_{1}}}}}}} \\ {= {{r_{2}\sqrt{1 - \left( \frac{\Delta \; X}{r_{2}} \right)^{2}}} - {r_{2}\sqrt{1 - \left( \frac{l_{2}}{r_{2}} \right)^{2}}}}} \end{matrix} & (10) \end{matrix}$

Therefore, the distance of the bias dl from an X-axis when an electron passes the point P₃ is expressed by Equation (9) and Equation (10) as follows.

$\begin{matrix} {{{dl} = {{r_{1}\left( {1 - \sqrt{1 - \left( \frac{l_{1}}{r_{1}} \right)^{2}}} \right)} + {D\frac{l_{1}}{r_{1} - {r_{1}\left( {1 - \sqrt{1 - \left( \frac{l_{1}}{r_{1}} \right)^{2}}} \right)}}} + {r_{2}\sqrt{1 - \left( \frac{\Delta \; X}{r_{2}} \right)^{2}}} - {r_{2}\sqrt{1 - \left( \frac{l_{2}}{r_{2}} \right)^{2}}}}}{{Here},}} & (11) \\ {r_{2} = {\frac{mv}{{eB}_{2}} = {\frac{m_{0}v}{e\sqrt{1 - \left( \frac{v}{c} \right)^{2}}} \times \frac{1}{B_{2}}}}} & (12) \end{matrix}$

The electron moves straight and reaches the point P₄ on the plane of the X-rays target without effect of the magnetic field after passing the point P₃. The tangential gradient of the point P₃ is given by the next equation.

$\begin{matrix} {\begin{matrix} {{\tan \; \theta_{2}} = \left\lbrack \frac{y}{x} \right\rbrack_{P_{3}}} \\ {= \frac{\Delta \; X}{l_{3}}} \\ {= \frac{\Delta \; X}{r_{2}\cos \; \theta_{2}}} \\ {= \frac{\Delta \; X}{r_{2}\sqrt{1 - {\sin^{2}\theta_{2}}}}} \\ {= \frac{\Delta \; X}{r_{2}\sqrt{1 - \left( \frac{\Delta \; X}{r_{2}} \right)^{2}}}} \end{matrix}{{Therefore},}} & (13) \\ {\theta_{2} = {\tan^{- 1}\left( \frac{\Delta \; X}{r_{2}\sqrt{1 - \left( \frac{\Delta \; X}{r_{2}} \right)^{2}}} \right)}} & (14) \end{matrix}$

When Δx=0, in other words the point P₃ is on an X coordinate same as the central point C₂ of the circle, the tangent in the point P₃ on the circular orbit is θ₂=0 in parallel to an X-axis. In other words, a high-speed electron can be incident in parallel to an each medial axis of the target tube 104-1 through 104-n by controlling the voltage in the electron gun 103 accelerating an electron and the magnetic flux density of the first deflection electromagnet 106 and the second deflection electromagnet 107.

FIG. 4 shows the X-ray target tube concerning the preferred embodiment 1 of the present invention. In FIG. 4, the X-ray target tube 104 which is registered by Japanese Patent No. 3795028 applied by this applicant is comprised such as a main body of the X-ray target tube 121 and a cover tube 122. The main body of the X-ray target tube 121 is formed the metal with heavy atomic weight, high-melting point, high chemical stability and superior thermal radiation characteristic, for example Au, W, MO, Pt, Re. The main body of the X-ray target tube 121 has the shape of the extremely thin truncated cone which has the diameter of an inlet aperture 123 is 1 mm, the diameter of an outlet aperture 124 is 0.5 mm and the overall length is 100 mm. The high energy electron beams are irradiated by the electron gun 103, the shape is the form of hollow doughnut that the outside diameter is approximately equal to the inlet aperture 123 and the inside diameter is approximately equal to the outlet aperture 124. X-rays are irradiated by high energy electron beams colliding with the inner wall of this X-ray target tube. The generated X-rays are total reflected and are irradiated as the extremely small radiation angular degree of the X-rays from the outlet aperture 124 because the incline of the inner wall of the X-ray target tube 121 is 0.143239 degree as the diameter of the target tube becomes 0.25 mm narrow at the length of 100 mm. The outside of the main body of the X-ray target tube 121 is covered with the cover tube 122. Holes 125 to discharge the gas which is generated by the collision of high energy electron beams are made in the main body of the X-ray target tube 121 and the cover tube 122. Even more particularly, the heat which is generated by the collision of high energy electron beams is cooled by such as a forced air-cooling or water-cooling.

FIG. 5 shows the dose distribution in the radiation field of the X-ray target tube concerning the preferred embodiment 1 of the present invention. In FIG. 5, the shape of the radiation field Fi of the X-ray target tube 104 is an approximately circular in a lesion department assumed the place of 50 cm from the outlet aperture 124. The X-ray intensity is approximately constant near a center of the radiation field, but the intensity decays sharply to zero around the radiation field. In the radiation field Fi of the X-ray target tube 104, as for the domain where the X-ray intensity is half value of the maximum, namely the radiation field Fhi of ½ width is a circle which the diameter is approximately 1 mm.

FIG. 6 shows the radiation field of the X-ray target tube array concerning the preferred embodiment 1 of the present invention. FIG. 6( a) shows the relationship between the radiation field of the X-ray target tube array 105 and the radiation field of each X-ray target tube 104 comprising the X-ray target tube array 105. FIG. 6( b) shows the dose distribution when X-rays of the same intensity are irradiated from each X-ray target tube. In FIG. 6( a), the X-ray target tube array 105 is comprised by the X-ray target tubes 104-1 through 104-n arranging in line so that the radiation fields of ½ width Fh1-Fhn of each X-ray target tube 104-1 through 104-n are formed without a clearance adjacently at predetermined distance, for example, is assumed the place of 50 cm in the lesion portion of a patient, from the outlet aperture 124. If it says in detail, the X-ray target tube array 105 is comprised by the X-ray target tube 104-1 through 104-n arranging so that the radiation field Fhi which is ½ width of the X-ray target tube 104-i adjoins the radiation field Fhi+1 which is ½ width of the X-ray target tube 104-i+1 and the radiation field Fhi−1 which is ½ width of the X-ray target tube 104-i−1. Thus, the radiation field of the X-ray target tube array 105 is comprised by F1 through Fn which are the radiation fields of the X-ray target tube 104-1 through 104-n. Hence, as shown in FIG. 6( b), when the radiation intensity of each X-ray target tube is the same, the whole X-ray radiation intensity can be approximately equal in the whole radiation field. For example, the X-ray target tube array which can irradiate to the domain of 50 mm*50 mm is comprised as follows. When the radiation field of ½ width in the distance of 50 cm is supposed a circle of a diameter of 1 mm from the outlet aperture of one X-ray target tube, the slim rectangular radiation field of 1 mm*50 mm is formed by arranging in line 50 X-ray target tubes 104-1 through 104-50. The radiation field of 50 mm*50 mm is formed by repeating 50 times to translate the radiation field of 1 mm*50 mm by 1 mm after the radiation. As for the method of translation of the radiation field, there are two methods of moving the X-ray target array and moving an irradiated object.

The X-ray dose intensity data of the treatment field and the radiation intensity data of the radiation field concerning the preferred embodiment 1 of the present invention are shown in FIG. 7. In IMRT, the dose required the treatment of the lesion portion and the ideal dose distribution which considers a neighboring normal cellular permissible dose is set first. Next, the shape of the radiation field, the radiation direction and the dose intensity of each divided radiation field are input into the therapy apparatus as a treatment plan data. FIG. 7( a) shows the two-dimensional dose intensity distribution which is required the treatment of the lesion portion viewing from 171 direction. FIG. 7 (b) shows the radiation intensity data 113 of a treatment field made according to the two-dimensional dose intensity distribution of the lesion portion in FIG. 7( a). The radiation intensity data 113 of a treatment field is subdivided to the radiation intensity data 112 (i, j) every X-ray target tube 104-1 through 104-n.

FIG. 8 shows the perspective view of the X-ray therapeutic apparatus attached X-ray generator concerning the preferred embodiment 1 of the present invention. As shown in FIG. 8, an X-ray therapeutic apparatus 181 comprises the X-ray generator 101-1 through 101-5 on five places of an O-type arm 182 which are at the top, the right slippage top, the right slippage bottom, the left slippage top and the left slippage bottom, a treatment couch 183 laying a patient in an inner side of the O-type arm 182, a transfer unit 184 moving the treatment couch 183 in the horizontal and a control unit 185 to control actuating of the transfer unit 184. The X-ray radiation apertures of X-ray generators 101-1 through 101-5 are attached for the lesion portion of the patient who is fixed on the treatment couch 183. The control unit 185 stores a treatment control program 186, a radiation control program, a radiation intensity data of the treatment field and a radiation intensity data of the radiation field. The X-ray therapeutic apparatus irradiates from five X-ray generators 101-1 through 101-5 simultaneously while moving the treatment couch 183 by 1 mm depending on an execution of the treatment control program 186, the X-radiation therapy is carried out.

FIG. 9 is a flow chart showing the routine of the radiation control program of the X-ray generator concerning the preferred embodiment 1 of the present invention. In the exposition of the flow chart of FIG. 9, the number of the radiation intensity data 112 comprising the radiation intensity data 113 of the treatment field shown in FIG. 7( b) is m, the number of the X-ray target tube 104 comprising the X-ray target tube array 105 is n, the number of the X-ray target tube 104 is i, the number of the radiation intensity data 112 of the field is j. The X-ray radiation is carried out from the radiation intensity data 112 (1, 1) to 112 (n, 1), the treatment couch 183 is moved 1 mm next, and the X-ray radiation is carried out from 112 (1, 2) to 112 (n, 2). After this, the X-ray radiation is carried out to 112 (n, m) according to the radiation control program 111 by repeating the same sequence. Firstly, as shown in the flow chart of FIG. 9, j=1, i=1 are set so that the X-ray radiation start to irradiate from the X-ray target tube 104-1 of i=1 to the X-ray target tube 104-n of i=n in turn according to the radiation intensity data 112 which is the radiation field of j=1 in the radiation intensity data 113 of the treatment field. The first deflection electromagnet 106 is excited so that the high energy electron beams irradiated from the electron gun 103 turns toward the inlet aperture 123 of the i-th X-ray target tube 104-i comprising the X-ray target tube array 105. The second deflection electromagnet 107 is excited by the exciting current which is the reverse phase for the first deflection electromagnet 106 so that the electron beam deflected with the first deflection electromagnet 106 penetrates parallel to the medial axis of the X-ray target tube 104-i. In the radiation intensity data 112 of the radiation field of j-th line, the width of the high energy pulse according to the radiation dose which is set by the i-th X-ray target tube 104-i is set. Afterwards, the high energy pulse is output at the suitable timing. As a result of this, X-rays with desired intensity is irradiated the lesion portion with the X-ray target tube 104-i. These a series of actuating is the same in the X-ray generator 101-1 through 101-5 in FIG. 8. After the high energy pulse have output, the radiation control program judges whether i=n, if still i≠n, as i=i+1, the excitation of the electromagnet, the output condition setting of the high energy pulse and the pulse outputting are repeated. If i=n, the radiation control program judges next whether j=m, if j≠m, the radiation control program is executed the j+1st line of the radiation intensity data 112 of the radiation field as j=j+1. At first, the treatment couch 183 is transferred 1 mm, the X-ray target tube 104-1 is set up. After this, the excitation of the electromagnet, the setting of the output condition for the high energy pulse and the outputting of the pulse are repeated to i=n. The above-mentioned sequence is repeated to i=n, j=m.

FIG. 10 is a flow chart showing the routine of the treatment execution program of the control unit concerning the preferred embodiment 1 of the present invention. As shown in FIG. 10, at first the X-ray generator 101-1 through 101-5 and the each part are initialized, the position of the treatment couch is set in accordance with set the value of i and j of the radiation control program 111. After this, the X-ray therapy is executed according to the radiation control program 111. It is judged whether the radiation control program execution of the X-ray generator 101-1 through 101-5 completed every one radiation, and the sequence is continued if the program execution does not still complete, and, as for the treatment, it is finished when the radiation control program execution of all X-ray generator completes.

FIG. 11 shows the perspective view of the other X-ray therapeutic apparatus attached the X-ray generator concerning the preferred embodiment 1 of the present invention to a gantry. As shown in FIG. 11, the X-ray therapeutic apparatus 191 attached the X-ray generator 101 to the radiation head 193 of the gantry 192 used for the conventional radiation therapy apparatus.

The X-ray therapeutic apparatus 191 comprises a treatment couch 194 to put a patient on and a transfer unit 195 moving the treatment couch 194 in the horizontal and a control unit 196 which is connected to the X-ray generator 101 and the transfer unit 195, carrying out X-ray therapy. The X-ray therapeutic apparatus 191, like conventional IMRT, turns the gantry 192 around the treatment couch 194 which put a patient centering on the isocenter of the lesion portion. The treatment couch 194 moves in parallel perpendicularly to the X-ray target tube array 105 of the X-ray generator 101 by the transfer unit 195. The X-ray generator 101 irradiates X-rays synchronously for transferring the treatment couch 194. The radiation intensity data 113 of the treatment field is divided adapting the rotation angle of the gantry 192 to the two-dimensional dose distribution 171 required the treatment of the lesion portion for the patient. The radiation intensity data 113 of the treatment field is set every the rotation angle of the gantry 192. While the treatment couch 194 irradiates X-rays corresponding to the radiation dose, is translated by 1 mm to the X-ray generator 101 by the transfer unit 195.

As explained in detail above, the X-ray generator 101 concerning detailed the description of the preferred embodiment 1 is comprised of the electron gun 103, the first deflection electromagnet 106, the second deflection electromagnet 107 and the X-ray target tube array 105. The Electron gun 103 irradiates high energy electron beams by a high energy pulse output from the power source 108. The first deflection electromagnet 106 and the second deflection electromagnet 107 change the direction of high energy electron beams so that high energy electron beams are incident in parallel with the medial axis of X-ray target tube 104-1 through 104-n, the high energy electron beams are incident on the X-ray target tube 104-1 through 104-n in turn. The X-ray target tube array 105 is comprised to bundle up a number of X-ray target tube so that field F1 through Fn of the X-ray target tube 104-1 through 104-n irradiating X-rays by the collide of high energy electron beams continues. The radiation intensity every X-ray target tube 104-i and the width of the high energy pulse output from the power source 108 are set by the radiation intensity data 113 stored in the controller 109. As for the timing to output the high energy pulse and the timing to excite the first deflection electromagnet 106 and the second deflection electromagnet 107 so that electron beam to generate by the pulse fits to the position of predetermined X-ray target tube 104-i, they are controlled by the radiation control program 111. In this way, the X-ray generator 101 concerning detailed description of the preferred embodiment 1 can obtain the X-ray dose distribution intensity modulated corresponding to the X-ray dose which is desired for treatment of each part of the lesion portion. Because, according to detailed description of the preferred embodiment 1, the radiation fields F1-Fn of X-ray target tubes 104-1-104-n are bundle up a number of several field to continue in a lesion department of the patient, the radiation field of the X-ray target tube array 105 comes to continue. Because, according to detailed description of the preferred embodiment 1, the radiation fields Fh1 through Fhn of ½ width of X-ray target tubes 104-1 through 104-n are bundled up so that the field of ½ width continues in a lesion portion of the patient, the composed radiation field of the X-ray target tube array 105 is to equal radiation intensity. In X-ray generator of detailed description of the preferred embodiment 1, the electron gun 103 outputs high energy electron beams when high energy pulse p-1 through p-n with pulse width corresponding to the required radiation dose are input. The electron beam collides to the inner wall of the X-ray target tube 104-1 through 104-n, and X-ray beams x-1 through x-n are irradiated. The X-ray generator 101 of detailed description of the preferred embodiment 1 is different from the conventional X-ray generator repeating multiple X-ray radiation using a multi-leaf collimator, and the two-dimensional dose distribution for the treatment can be obtained immediately. Because it is not necessary to adjust a multi-leaf collimator for the X-ray radiation with detailed description of the preferred embodiment 1, the time to need for treatment can be shortened. Hereby, the burdens of the patient can be eased.

Detailed Description of the Preferred Embodiment 2

Next, the X-ray generator concerning the preferred embodiment 2 of the present invention is explained. FIG. 12( a) shows the constitution of the X-ray generator concerning the preferred embodiment 2 of the present invention. About the intersection of detailed description of the preferred embodiment 1 is shown with the same number. The characteristic of the X-ray generator concerning this detailed description of the preferred embodiment 2 is to irradiate the high energy electron beams while scanning to the X-ray target tube array 205 arranging the X-ray target tube 104 in a matrix state as shown in FIG. 12( b). Even more particularly, a characteristic of the X-ray generator concerning this detailed description of the preferred embodiment 2 is that the high energy electron beams deflected by an deflection electromagnet 206 are able to be incident parallel to a medial axis of each X-ray target tube 104 (i, j) of the X-ray target tube array 205 by changing the shape of the inlet aperture plane of the X-ray target tube array 205 radially. As a result of this arrangement, for example, the radiation field of X-ray target tube array 105 can be formed radially to 50 mm*50 mm in the position of 50 cm away from the outlet aperture. To realize the X-ray generator concerning this detailed description of the preferred embodiment 2, in the X-ray generator concerning detailed description of the preferred embodiment 1, it is replaced the first deflection electromagnet 106 and the second deflection electromagnet 107 deflecting one dimensionally the direction of high energy electron beams that the quadrupole electromagnet 206 which the two-dimensional deflection is possible.

FIG. 13 shows the cross-sectional view which cut the quadrupole electromagnet with the face (X-Y axial plane) which is perpendicular to the direction (Z-axis course) of the electron beam. In FIG. 13, the quadrupole electromagnet consists of the four magnetic cores 131 a through 131 d and the magnetizing coils 132 a through 132 d wound up to each magnetic core. A magnetic field generates in the direction shown with the dotted line arrow in FIG. 13 by spreading exciting current in the coil. The direction of the magnetic field can be set the opposite direction by reversing the polarity of the exciting current. In FIG. 13, when high energy electron beams were incident on the Z-axis direction (from front to back of the space), Lorentz force works in the direction of the solid line arrow. Thus, by control of the excitation current magnitude and the polarity, the course of electrons can be deflected in the arbitrary direction of the X-Y axial plane. The electrons via the magnetic field of the quadrupole electromagnet go straight on, and reach the inlet aperture plane of the X-ray target tube array 205. The X-ray target tube 104 (i, j) is arranged a matrix state as shown in FIG. 12( b), even more particularly, the inlet aperture plane is placed radially so that the electrons which went straight on after being deflected by the quadrupole electromagnet are incident for a medial axis of the X-ray target tube 104 (i, j) horizontally. Thus, the X-rays irradiating from the X-ray target tube array 205 is irradiated radially, the radiation field is formed as shown in FIG. 14. The radiation field of each target tube 104 (i, j) comprising the radiation field of the X-ray target tube array 205 is formed so that the radiation fields of ½ width are adjacent like the case of detailed description of the preferred embodiment 1.

In detailed description of the preferred embodiment 2, because the radiation of X-ray target tube 104 (i, j) is adjacent a matrix state, the adjacent ways such as the case which ½ width of the radiation field adjoins with four places as shown in FIG. 14( a) and with six places as shown in FIG. 14( b) are considered. For example, in the case that the radiation field of 50 mm*50 mm is formed by the place of 50 cm from the outlet aperture of the X-ray target tube array 205, the diameter of ½ width of the X-ray target tube 104 is supposed to be 1 mm, when the configuration adjoining with four places of the adjacent X-ray target tube is adopted, the X-ray target tube array 105 is comprised with 250 X-ray target tubes. The radiation intensity of each X-ray target tube 104 (i, j) is based on the radiation intensity data 112 of the radiation field set beforehand like detailed description of the preferred embodiment 1. The order of scans when X-rays irradiate can select the form, such as the scanning from the center for the outside course of the radiation field, the scanning to begin from the circumference to leave for the center and the scanning of the direction of row or column from one corner for the other corner, to respond the operating condition. As discussed above, according to detailed description of the preferred embodiment 2, because X-ray target tube arrays are arranged radially, the radiation field can be formed planate widely. Thus, a treatment time can be shortened more than the X-ray therapeutic apparatus concerning detailed description of the preferred embodiment 1 without moving the X-ray generator or the treatment couch which a patient was put on, the X-ray therapeutic apparatus which is suitable for IMRT can be provided.

The X-ray generator concerning the present invention and the X-ray therapeutic apparatus which applies the X-ray generator can utilize for the X-ray therapeutic apparatus which is suitable for IMRT in a medical field. The X-ray generator concerning the present invention can be utilized for a nondestructive inspection system and an X-ray analysis device in an industrial field. 

1. An X-ray generator, comprising: a power source outputting high energy pulses; an electron source irradiating high energy electron beams by the high energy pulses; a microwave source supplying a high voltage microwave to the electron source; an X-ray source bundling up a plurality of X-ray tubes irradiating X-ray by a collision of the high-energy electron beams, arranging to continue the radiation fields of the X-ray tubes; a deflection means deflecting the direction of the high energy electron beams so that the high energy electron beams are incident in parallel to the medial axis of the X-ray tubes, and are incident on the X-ray tubes sequentially; a data setting the radiation intensity of the X-ray tube so that the predetermined dose distribution is obtained in the field of the X-ray tube; and a control means setting up the high energy pulse width according to the radiation intensity data, synchronizing a timing to output the high energy pulse and a timing to irradiate the electron beams and a timing to excite the deflection means.
 2. The X-ray generator of claim 1, wherein the deflection means comprises a first deflection electromagnet deflecting the high energy electron beam to an inlet aperture of any X-ray tubes and a second deflection electromagnet deflecting the high energy electron beams deflected by the first deflection electromagnet so that the high energy electron beams are incident in parallel to the medial axis of the X-ray tubes.
 3. The X-ray generator of claim 1, wherein the X-ray source comprises the X-ray tubes arranging in line, the high energy electron beams are sequentially irradiated from one end of the X-rays tubes to the another end.
 4. The X-ray generator of claim 1, wherein the deflection means comprises a deflection electromagnet deflecting the high energy electron beam to an inlet aperture of any X-ray tubes and the X-ray tube arranging radially so that the direction of the high energy electron beams deflected by the deflection electromagnet are in parallel to the medial axis of the X-ray tubes.
 5. The X-ray generator of claim 4, wherein the deflection means comprises a quadrupole electromagnet.
 6. The X-ray generator of claim 1, wherein the X-ray tube comprises a truncated cone shape having a smaller diameter of the outlet aperture than the inlet aperture, and acts as an X-ray target tube irradiating X-ray beams by the collision of high energy electron beams with the inner wall of the X-ray tube.
 7. The X-ray generator of claim 1, wherein the X-rays source comprises the X-ray tubes arranging so that radiation fields of ½ width for the maximum radiation intensity are adjacent in succession.
 8. An X-ray therapeutic apparatus comprising the X-ray generator of claim 1, further comprising The X-ray generator, wherein one or more the X-ray generators being installed in different positions of the three-dimensional space including the treatment couch, X-rays are irradiated intensively on the lesion portion of a patient fixed on the treatment couch in the space.
 9. The X-ray generator of claim 1, applied to the X-ray therapeutic apparatus, wherein the X-ray generator is applied to the X-ray therapeutic apparatus being able to vary a relative position of the lesion portion of a patient fixed on a treatment couch and the X-ray generator installed in an X-ray head, irradiating X-rays to the lesion portion of the patient. 